Injection site for male luer or other tubular connector

ABSTRACT

A medical device has an interior for containment of fluids; an opening into the interior, an elastomeric wall comprising a fixedly placed, flexible barrier across the opening; and a retention wall positioned adjacent to a peripheral portion of the elastomeric wall. The retention wall defines a central opening and has a generally rigid retention zone surrounding the central opening, to engage and retain a connector tube which is advanced into the central opening to displace the elastomeric wall and to open a flow aperture through the elastomeric wall, for flow through the wall and connector tube. One of the retention zone and connector tube are made of a material of sufficient hardness that material of the other engaging member is deformed by engagement therewith, which increases the strength of retention between the retention wall and the connector tube.

BACKGROUND OF THE INVENTION

Tubing sets for the transfer of medical fluids such as blood or parenteral solution generally comprise flexible plastic tubing with end connectors, which are often luer-type connectors. Injection sites are often carried on the tubing at the ends of, or between the ends of, the tubing sets, comprising an elastomeric diaphragm or bung which is carried in a housing in typically compressed or restrained fashion, so that a needle can resealably penetrate the elastomeric bung and communicate with the interior of the tubular set, for administration of medicines and the withdrawal of medical samples such as blood. Also, in the field of extracorporeal blood transport, in which blood is conveyed to and from an extracorporeal blood processing device such as a dialyzer or an aphaeresis apparatus, such an injection site may also be used to add parenteral solution such as normal saline.

As a disadvantage, a needle cannot connect with a luer connection and vice versa. The Medic® Universal Connector of Medisystems Corporation, described by U.S. Pat. No. 5,071,413, is a device which is capable of alternatively penetrating an elastomeric diaphragm and joining with a female luer site. However this device is not suitable in all uses. For example, an injection site on a flexible tube set may not fit with the Medic design because the Medic device is too long, and impinges the opposite wall of an injection site carried on tubing, having an entry direction perpendicular to the axis of the tubing.

As a further disadvantage, there may be a need to make a connection through an elastomeric diaphragm injection site using a tube which is terminated in a male luer connector. Present means for doing this are cumbersome. See U.S. Pat. Nos. 5,242,393 and 6,344,033.

By this invention, a connection system is provided for typically medical devices, including vials and containers for medicine, liquid, or gas, and also injection sites mounted on tubing sets. This system is capable of establishing connection with a male luer, including many ISO compatible, commercially available male luer lock connectors, while it is also preferably capable of providing resealable needle connections. Non-luer tapered tubes may also be connected with the system of this invention.

DESCRIPTION OF THE INVENTION

In accordance with this invention, an injection site is provided as part of a medical device which has an interior for containment of a fluid (liquid or gas). For example, the medical device may be a drug vial or container which utilizes the injection site of this invention, or it can be a tubing set having a main flow path for blood, parenteral solution, gases, or the like, to permit access preferably either by a male luer (luer slip or luer lock) connector or other type of tubular probe, without any intermediate device as in the prior art, such access being to the flow path of the tube set or the interior of any other container. Preferably, access through the injection site is also available as well by a needle, sharp or blunt.

An opening is defined into the interior of the medical device, with an elastomeric wall forming a fluid/air tight barrier across the opening, preferably both at positive and negative pressures relative to atmosphere. The elastomeric wall typically defines a compressed, or at least constrained, sealed perforation extending at least nearly therethrough. This perforation may be a closed slit with one or many branches, as in the form of a star (*). It may comprise one or more curved slits, or a simple, straight slit. Optionally, a retaining skin or skins made of another material, or wall material, may prevent complete opening and passage of fluid through the perforation until desired. Also, typically, the elastomer wall is compressed generally at its periphery, to cause pressurization of the perforation so that there is better sealing through the slit and some resistance to opening. Alternatively, it is possible to co-mold the elastomer part and the housing parts in one operation, and in this and other instances the elastomer wall will not be compressed at its periphery, since it will be held by the molded part in non-compressed condition. Also wall materials may preferably be used that exhibit cohesion or tackiness between the edges of the slit or perforation to hold it together in releasably closed position.

A retention wall is provided, being generally rigid and nonelastomeric, and positioned adjacent to, or in relative proximity to, a peripheral portion of the elastomeric wall. The retention wall may be either spaced from or in contact with the elastomeric wall, being typically spaced by no more than one cm., so as to remain adjacent to the elastomeric wall. The retention wall has a retention zone surrounding a central opening, to engage and retain a connector tube having a leading end, which is advanced into said central opening to displace the elastomeric wall and to open a flow aperture through the elastomeric wall, for flow through said wall and connector tube. The flow aperture may be provided by a pre-formed perforation, or the connector tube may have a sharp point or edge to open a flow aperture by cutting through an elastomeric wall which does not have a perforation.

Alternately, the retention wall may be placed spaced from the elastomeric wall such that said elastomeric wall is first penetrated by the connector tube prior to engaging with the retention zone.

At least part of the retained connector tube and the retention zone may be made of a material of sufficient hardness that material of the other of the retained connector tube and the retention zone is deformed, temporarily or permanently, by engagement of the two elements, to increase strength of retention (i.e. resistance to disconnection) between the retention wall and the connector tube. Such a strength increase resulting from the deformation may preferably be at least about 100 grams of force required for such disconnection.

Also it is preferred for the retention zone to be sized to engage and hold the connector tube before the connector tube's leading end completely penetrates the elastomeric wall, although the connector tube may have penetrated sufficiently to open the perforation in the elastomeric wall. This can be accomplished in various ways. In one preferred embodiment, the connector tube may be an ISO standard male luer connector tube that tapers outwardly from its outer or leading end to its inner base. Thus, in the embodiments described, the advancing connector tube comes into engagement with the retention zone, where it may be stopped and held, with material deformation to increase the strength of retention, as the connector tube opens the perforation in the elastomeric wall, but before the leading end or outer tip of the connector tube passes beyond the material of the elastomeric wall. This condition is shown in all of the specific embodiments of the drawings, including FIG. 13.

Advantages of this include the fact that, with such limited penetration, the connector tube will not project far into the area inside of the elastomeric wall, which may comprise a blood flow path. Such penetration can cause turbulence, and can reduce the laminar flow of blood through the blood flow path, which is undesirable. Also, such limited penetration, while effective to achieve fluid flow through the elastomeric wall, permits a smaller device to be designed and used, compared with systems where full penetration of the elastomeric wall by the connector tube takes place. Also, as is illustrated in the preferred embodiment of FIG. 13, there are laminar flow advantages available to a connector tube that does not fully penetrate the elastomeric wall. The almost-penetrated elastomeric wall serves as a transition and flow guide between the annular end face of the connector tube and the lumen wall of the adjacent connector bore. In typical male/female connector sets, the flow path must exhibit a “step out” from the connector tube to the adjacent bore with significant pressure losses, dependant on the size of the annular face. By this invention, such a step is largely avoided, thus reducing turbulence.

Preferably, the retention zone may be ring-shaped, and may have an axial depth (i.e. its dimension in the generally axial direction of the retained connector tube) of no more than about 3 mm. In some embodiments, the retention wall may comprise a transverse wall having an aperture that defines the central opening with a thickness of no more than about 1 mm, so that the edge of the wall that defines the central opening can dig into and deform a portion of the retained connector tube, which connector tube may typically be conical in shape. As one advantage of such a configuration, the molding tolerance of the respective parts can be relatively low when compared with a luer connection. For example, it is generally necessary for the retained connector tube to be positioned in its engaged and retained position with its tip extending into engagement with the elastomeric wall to deflect the elastomeric wall, (or optionally to penetrate it) to open the perforation of the elastomeric wall so that flow communication can take place through the elastomeric wall and the retained connector tube. However, the overall dimensions and the longitudinal position of the connector tube may have a certain amount of variability (tolerance) and it still may be advanced into engagement with the elastomeric wall, with material deformation taking place by engagement of the connector tube and the retention zone and the necessary position achieved. Thus, the parts of the device are easier to manufacture.

This is particularly important in the case where the retained connector tube is part of an ISO male luer lock connector, where the luer of such connectors only extends a short distance beyond its locking sleeve (such as 2.1 to 3.5 mm), and the advancement into engagement with an elastomeric wall is thus of limited distance. In this embodiment, the male luer does not penetrate completely through the elastomeric wall, but merely may displace it by a distance sufficient to stretch open the perforation of the elastomeric wall. Upon such advancement, the retention zone surrounding the central opening forcefully engages the male luer of the luer lock connector, with deformation of material resulting through such engagement in one, or the other, or both parts, to increase the strength of retention between the retention wall and the male luer connector tube, so that the natural resilience of the displaced elastomeric wall does not force expulsion of the connector tube from the retention zone, and a stable, open flow path is created. This arrangement is especially good for connectors used in blood flow tubing, since a turbulence and clot promoting male luer tip in the blood flow path is avoided.

Preferably, the material of one of the retention zone and the connector tube is harder than the material of the other part, to facilitate deformation of material as engagement between the connector tube and the retention zone takes place, resulting in increased strength of retention between the retention wall and the connector tube. Depending on the design and nature of the materials, this engaged and retained relationship between the connector tube and the retention zone may be permanent or temporary, but preferably is of sufficient strength that accidental separation does not take place. Typically, the retention zone is harder than the connector tube, having a Shore A durometer of at least about A80.

In some embodiments, a plurality of typically radial spaces may divide the retention zone into separate sections, to provide for greater flexibility of the material of the retention zone, for example, as when the retention wall and retention zone are made of a metal, such as stainless steel. In such a situation, separate tabs of the retention zone engage the connector tube and dig into the material of the connector tube, for firm retention as the tip of the connector tube displaces a central portion of the elastomeric wall and opens a perforation defined therein, for fluid communication through the wall and connector tube.

Typically, the axial distance by which the connector displaces the elastomeric wall at its center is on the order of 1 to 6 mm, in those circumstances where the connector tube does not penetrate through the elastomeric wall perforation, but its front end presses axially against the surface of the elastomeric wall, generally with a closed loop line of pressure positioned on the elastomeric wall, typically radially beyond any portion of the perforation, to provide a closed sealing area between the end of the connector tube and the elastomeric wall.

If the connector tube does displace the elastomeric wall further, but without the front end actually penetrating beyond the perforation slit, an added seal may be provided between the connector tube side wall and the surface of the elastomeric wall. The connector tube may further displace the elastomeric wall where the front end of the connector tube does penetrate through the perforation of the elastomeric wall, in which case the only seal remaining may be provided between the connector tube and the material defining the perforation. The perforation may be proportioned in some embodiments to provide a 360 degree seal about the connector tube side wall, to provide a seal in a different way from abutment of the tip of the connector tube against the elastomeric wall around the area of the perforation, as discussed in the last paragraph.

Also, as illustrated in the drawings, a combination of the above two seals may be obtained, where the front end of the connector tube presses against the elastomeric wall, and deflects the elastomeric wall to a degree that the wall provides a second 360° seal about the connector tube sidewall. See particularly, FIGS. 11–13 for this feature.

In some embodiments, the perforation may comprise a line having a length of about the outer diameter of a male ISO luer at a point adjacent to its minimum diameter end, which line can stretch to provide the desired 360 degree seal as the luer penetrates into the perforation. Such a system may be used with a luer slip or a luer lock system.

In some embodiments, upper and lower retention wall portions for holding the elastomeric wall may respectively define upper and lower central apertures which are positioned generally coaxially with each other. The lower central aperture may be of greater diameter than the upper central aperture, which facilitates inward displacement of the elastomeric wall by the connector tube, to cause opening of the perforation. The retention zone may then defined around the central upper aperture. Typically, the lower central aperture is rarely smaller than a 4 mm inner diameter, and may need to be larger, so as to allow enough “doming downward” of the elastomeric wall to allow sufficient stretching by an ISO male luer which has a leading outer diameter of 3.975±0.025 mm. Alternatively, the lower retention member may exist on its own, without an upper retention member, and a dimensioned to grip the side wall of the connector tube with or without a stretched, displaced elastomeric wall intervening between the connector tube and said lower retention member.

In some embodiments, there may extend outwardly from the elastomeric wall and the retention wall a tapered-bore tube having opposed, longitudinal slots, to permit easier antiseptic swabbing of the interior and the outer face of the elastomeric wall, at the same time providing locking connection to a connector tube. Alternatively, such a tube may have a cylindrical bore or a counterbore with or without such slots or it may comprise a female luer or luer lock device.

It can also be seen that it is generally possible to make connection through the injection site of this invention by conventionally using a hypodermic needle, where the sharp needle passes through the body of the elastomeric wall in normal piercing fashion, or through the at least partially preformed slit. When such a slit is used, it may be possible for a dull point needle to be used for connection.

As stated above, locking systems may be utilized as additional structure for connection so that accidental connector separation can be further eliminated as a risk.

Alternatively, the retention wall and retention zone described above may also be made of a fairly resilient material, so that it does some or all of the deformation, when engaging with the retained connector tube, to have the effect of increasing strength of retention between the retention wall and the connector tube.

Certain IV and hemodialysis sets which are sold by Japan Medical Supply and Kawasumi Laboratories disclose transversely-mounted injection sites which comprise slit elastomeric walls, compressed to reseal. The elastomeric wall is partially covered by a top wall in one case, having a central aperture large enough to receive a conventional male luer, which luer can penetrate completely through the elastomeric wall because of the presence of the slit, and the retention wall provides no restriction against said penetration. Neither of these designs can be opened for two way flow by known ISO standard male luer lock connector designs, even with prior penetration of the slit by another object including an ISO standard male luer lock connector. Nor can male luer locks be retained by the aperture in the top wall of the housing, nor are male luer slips retained by the aperture in the top wall of the housing while avoiding complete elastomeric wall penetration.

The JMS injection site requires the use of a non-ISO intermediate connector, called a Planecta, that fits to a male luer lock at one end and locks to the external housing of the injection site in a bayonet-type fitting.

By this invention, a direct connection can be made with an injection site of this invention and a male luer connector, or a male luer lock connector, particularly those of ISO standard, without any need for an intermediate connecting component. Preferably connection can also be made with a sharp or dull needle, not necessarily in any locking or retained relationship. The inventive injection site, contrary to those of the prior art, is thus capable of providing a direct connection at any time with any of the components listed below, so that the injection site can be connected with a wide variety of conventional medical sets and other items, providing a wide compatibility of use of a medical device which carries the injection site of this invention. The injection site of this invention may be used with an essentially unlimited variety of medical devices, whenever aseptic access is desired. For example, as shown, the injection site may be carried on any of a variety of tube sets in the manner of a T connector as shown in FIGS. 1 and 2, or at a tube end. The injection site may be used on an adaptor of various kinds, a stopcock, or as the stopper in any kind of container or vial for typically medical materials.

A preferred injection site of this invention comprises a housing having an interior, an opening to the interior, and an elastomeric wall which comprises a barrier across the opening. The elastomeric wall has a central area which defines a sealed perforation extending at least nearly therethrough. In other words, if the perforation does not extend all the way therethrough, a thin skin layer remains to provide sealing until it is opened by the connector tube as described above, which typically may be a male luer, either a luer slip or part of a luer lock connector, passing therethrough or sufficiently stretching the thin skin until it tears open. This skin layer does not need to be an elastomer, and may fracture when the wall is stretched by the pressing connector tube. For example, the skin layer may be a lacquer paint layer.

As another possibility, the sealed perforation of the elastomeric wall may not open at all when connection is made with a connector tube. However, the original seal of the perforation, which is strong enough to seal against substantial positive or negative pressure, is weakened by the deflection of the elastomeric wall by the connector tube so that, while still closed, its pressure resistance may be low. Then, flow takes place typically at relatively low fluid pressures normally encountered in medical fluid handling, so that fluids can be passed through the elastomeric wall between the connector tube and the injection site of this invention, but resealing takes place when the pressure on both sides of the elastomeric wall are equalized. Such resealing takes place until the pressure differential is created again for added flow. Also, in some embodiments, the shape of the elastomeric wall may comprise a one-way valve, so that pressurized flow at relatively low pressures normally takes place in only one direction and not in the other direction.

In some embodiments, a retainer cap comprising upper and lower retaining member portions retains the elastomeric wall fixedly in its barrier position across the opening. The cap defines an area which is typically annular, and which surrounds the central area of the retainer cap. The annular area may have an inner diameter of about 4 to 8 mm and a first upper, peripheral surface. The central area of the elastomeric wall may have a second, upper surface, with a relative level of the second upper surface being no lower than the level of the first upper surface. Because of this, when particularly an ISO standard male luer connector is advanced to open the injection site, the outer, annular end of the male connector skirt can rest against and form the closed loop seal that surrounds the central area, and the central male luer, which projects beyond the connector skirt by a predetermined amount, distorts the elastomeric wall sufficiently to open the sealed perforation for fluid communication through the barrier.

Furthermore, the central area of the elastomeric wall may typically have a thickness of no more than 3 mm. Also, it is generally preferred for the second upper surface (of the central portion of the elastomeric wall) to have a level that is above the level of the first, upper surface of the closed loop area against which the male luer lock connector may abut. This provides more distance of displacement of the elastomeric wall when it is opened, when compared with prior art injection sites.

DESCRIPTION OF THE DRAWINGS

In the drawings, FIG. 1 is a longitudinal sectional view of an injection site of this invention mounted on a tubular section, for connection with other tubular sections to form a tubular set for medical fluids.

FIG. 2 is a longitudinal sectional view of the injection site of FIG. 1, shown to be in connection with an ISO male luer lock connector carried on a syringe.

FIG. 3 is a longitudinal sectional view of an injection site and connector of this invention, carried on one end of a housing which, in turn, connects with an end of flexible tubing of a medical tube set.

FIG. 4 is a plan view of the retention wall used in FIG. 3.

FIG. 5 is a longitudinal sectional view of the injection site and connector of FIG. 3, shown to be in connected relation with an ISO male luer connector, which is attached to a syringe.

FIG. 6 is a vertical sectional view of another embodiment of this invention.

FIGS. 7–9 are longitudinal sectional views of another embodiment of an injection site and connector of this invention.

FIG. 10 is a longitudinal sectional view of another embodiment of an injection site and connector of this invention, shown in separated relation with a conventional luer slip connector.

FIG. 11 is a longitudinal sectional view showing the components of FIG. 10 connected together to provide a flow connection between them.

FIG. 12 is a longitudinal sectional view of a similar embodiment of the injection site and connector of this invention, with modification, and connected to a conventional luer lock connector.

FIG. 13 is a longitudinal sectional view of another embodiment of the injection site of this invention shown to be connected to a luer lock connector having a rotatable, threaded luer lock sleeve.

DESCRIPTION OF SPECIFIC EMBODIMENTS

Referring to the drawings, FIG. 1 shows a medical device 10 which comprises both a connector for a male luer or other tube, and an injection site. Device 10 shows a length of typically rigid tubing 12 which has an interior 14 for containment of fluid. Tubing 12 may connect at either end with lengths of flexible set tubing for blood or parenteral solution. For example, the sets which carry generally rigid tube 12 may be arterial or venous sets for hemodialyisis, pheresis, or the like.

Tube 12 defines a lateral opening 16 to the interior and a fixedly placed, flexible barrier 18, which may be an elastomeric wall extending across the opening.

A retention wall 20 is positioned adjacent to a peripheral portion of elastomeric wall 18, comprising an outer housing portion which may be heat welded to an annular rib 22 of tubular housing 12. Retention wall 20 defines a central opening 24, which exposes a central portion 26 of elastomeric wall 18.

Retention wall 20 defines an annular retention zone 28 surrounding central opening 24, to engage and retain a connector tube 34 which is advanced into the central opening, as shown in FIG. 2.

Specifically, FIG. 2 shows a male luer lock connector 30 carried on the end of syringe 32, and defining male luer (connector tube) 34 and threaded locking sleeve 37. Specifically, luer lock connector 30 is of dimensions and other characteristics which are compatible with the standards of the ISO (International Standards Organization) as are most luer connectors available for clinical use.

As seen in FIG. 2, connector tube 34, which is the male luer, advances through central opening 24. As connector tube 34 advances, it displaces elastomeric wall 18 and opens a flow aperture 36 a by expanding preformed slit or perforation 36, which is previously formed in elastomeric wall 18. However, in this embodiment tube 34 does not enter slit 36. At the same time, annular retention zone 28 of retention wall 20 is made of a plastic or metal which is hard enough to cause deformation of the plastic of male luer connector tube 34. Because of such deformation, there is an increase in the strength of retention at the junction between retention zone 28 and male luer 34, so that luer connector 30 is not readily withdrawn from its position shown in FIG. 2, without the intentional use of substantial withdrawing force, this being despite the fact that elastomeric wall 18 has a natural elastic resistance to its position shown in FIG. 2, and thus urges male luer connector outwardly. Thus, retention is provided at the junction between retention zone 28 and connector tube 34. Accordingly, syringe 32 may be held in flow connection with tube 12, which is typically part of a medical fluid flow set, so that desired materials may be passed into the flow set which carries tube 12 from syringe 32.

Retention wall 20 and annular retention zone 28 may be molded of an acrylic material, particularly, Cryolite Med 2 modified acrylic plastic, manufactured by Cryo Industries of Rockaway, N.J., having a Rockwell M hardness of 33. This is harder than the typical polypropylene of which a typical male luer connector may be manufactured, so that deformation of male luer 34 can take place, to strengthen the retention between retention wall 20 and male luer 34 when they are joined together as in FIG. 2. Tubular housing 12 may also be made of an acrylic material.

As a further advantage, if the flowing fluid in the set which comprises tube 12 is blood, little turbulence and flow blockage is provided by the connector of this invention, less than an inwardly projecting spike, for example, Hence, fluids may be added to the set without disrupting a laminar flow path through the set, which facilitates the reduction of blood clotting.

Syringe 32 may then be separated by a positive twist and pull from the injection site comprising retention wall 20, and elastomeric wall 18 closes slit 36 again for sealing of the system.

Alternatively, the injection site comprising retention wall 20 also permits needle access, both by a sharp needle penetrating through the elastomeric wall 18, or a dull needle, which can pass through slit 36.

The vertical thickness of the annular retention zone 28 which extends around connector tube 34 can be about one millimeter or less. Also, an internal, annular thinner edge may be defined at the retention zone 28 to facilitate the deformation of material. That strengthens the retention between retention wall 20 and connector tube 34, with the annular edge digging into the outer surface of connector tube 34.

Referring to FIGS. 3–5, another embodiment 40 of the medical device of this invention is carried on the end of tube 42, which may be a molded structure capable of receiving a flexible tube of a medical tube set for blood or parenteral solution, and serving as an injection site. Tube 42 may also comprise part of a Y site, a T site, or the like.

Tube 42 terminates in a generally rigid head portion 44, which comprises an annular support surface 46 for carrying the peripheral portion 48 of elastomeric wall 50. Elastomeric wall 50 may have an optional perforation 52, or it may comprise an intact wall, which is perforated immediately prior to use, for example, either by a separate, pointed instrument or by a tube generally of the shape of a male luer, but with a spike carried on the front end. Elastomeric wall 50 comprises the fixedly placed flexible barrier, being retained in position by retention wall 54, which may comprise a metal or plastic cap having a central aperture defined by closed loop retention zone 56 of retention wall 54. It can be seen that retention zone 56 comprises a small inner, bent, annular portion so that inwardly facing, sharp, annular edges may be defined.

FIG. 4 comprises a plan view of retention wall 54, showing central opening 58 and the inwardly facing, annular retention zone 56. In this embodiment, retention zone 56 comprises a material having a hardness of at least about Shore A 90, and divided into separate sections by radial slots or spaces 60, so that the individual separate retention zone sections 59 exhibit a measure of flexibility, but are still rigid enough to exhibit strong retentive characteristics against a connector tube 34 a with which they engage as the tube enters into central opening 58, deforming material of connector tube 34 a for strengthened retention.

Such an entrance by connector tube 34 a is shown in FIG. 5. As in the previous embodiment with respect to luer lock connector 30, this luer lock connector 30 a is connected to a syringe 32 a, and comprises the male luer 34 a and a threaded locking sleeve 37 a in conventional manner.

As shown in FIG. 5, the connection is made by forcing male luer 34 a inwardly within annular retention zone 56, until outer, annular end 62 of locking sleeve 37 a abuts retention wall 54. The advancing male luer 34 a, being of frustoconical shape, tightly engages retention zone 56 on such advancement, with deformation of plastic material at the junction area 56, to increase strength of retention between retention wall 54 and male luer or connector tube 34 a, to provide a locked connection, which may be a releasable lock if desired. This also causes the displacement of the central portion of elastomeric wall 50 by male luer 34 a, in a manner similar to the previous embodiment, resulting in the opening of perforation 52, which opens a fluid flow path between tube 42 and syringe 32 a.

When it is desired to withdraw syringe 32 a, it can typically be simply pulled or twisted and removed, and elastomeric wall 50 springs back into its normal position of FIG. 3, closing perforation 52.

It should be noted that in its natural configuration as shown in FIG. 3, the upper, central surface 53 of elastomeric wall 50 is elevated relative to the corresponding upper surface of the peripheral portions of the elastomeric wall, and it even may project above retention wall or retainer cap 54. As previously stated, this permits greater deformation of elastomeric wall 50 when a luer lock connector 30 a is brought into engagement as in FIG. 5 which, in turn, can provide better opening of perforation 52.

Referring to FIG. 6, injection site 70 is shown, being generally similar in structure and function to the previous injection sites disclosed, except as otherwise specifically described herein. Container or syringe 32 b, having a male luer lock connector 30 b comprising locking sleeve 37 b and male luer 34 b, is shown to be in connection with injection site 70. Container or syringe 32 b may be identical to the previous containers or syringes 32 and 32 a as shown in previous drawings.

In this particular embodiment, retention wall 72 comprises a plastic plate, carried integrally with a molded cap member 74, which serves to hold elastomeric wall 50 b in the desired position on annular seat 76, so that the periphery of elastomeric wall 50 b may be compressed and retained in desired position. Wall 50 b is carried on head portion 44 b, which defines a lateral opening 16 b in molded tubular component 12 b which is a tubular structure which may be connected at both ends with lengths of flexible tubing of a flow set for blood or parenteral solutions. Cap member 74 may be solvent sealed, snapped over, or otherwise bonded to head portion 44 b for nonremovability during normal use.

In this embodiment, cap portion or cover 74 has an upstanding sleeve 78, which is without threads or other structure, for retention of male luer lock member sleeve 37 b. It can be seen that male luer 34 b extends through an aperture in retention wall 72, with retention wall 72 being made of plastic, metal, or the like. As ISO standard male luer connector 34 b passes through the aperture defined by retention wall 72, its outer wall attains greater dimension by its conical nature, until locking sleeve 37 b enters into engagement with retention wall 72. At the same time, male luer 34 b, typically projecting outwardly beyond locking sleeve 37 b by approximately 2.1–3.5 mm., deflects the central portion of elastomeric wall 50 b to open perforation 80 in a manner similar to the previous embodiments. The outer wall of male luer member 34 b forceably engages retention zone 28 b, to cause the deflection of material at the annular junction site (28 b) to cause deformation of material of one or the other components at the annular junction site 28 b, to increase the strength of the bond between syringe 32 b and connector device 12 b. In the connected configuration, slit 80 opens, for flow communication through slit 80 and male luer 34 b to and from the interior of tube 12 b.

The forward advancement of luer 34 b is governed by the diameter of the aperture defined by retention zone 28 b. Thus, the degree of distention of elastomeric wall 50 b can be controlled so that luer 34 b does not overstretch slit 80 and enter into it, when that is desired. Also, the formation of an annular seal line 82 between the outer end of male luer 34 b and the upper surface of elastomeric wall 50 b provides a further, desirable sealing of the flow path through perforation 80 and male luer 34 b.

The impinging relation between retention zone 28 b and male luer 34 b can cause material deformation, typically in male luer 34 b when annular retention zone 28 b is made of harder material, to provide frictional and mechanical retention between the two pieces, so that they are not easily separated by accident. Retention wall 72 may be made of a plastic that is harder than the plastic of male luer 34 b, although the opposite may be utilized when desired, to obtain similar results.

Also, as luer lock connector 30 b is advanced to the position shown in FIG. 6, the outer wall of luer lock connector sleeve 37 b can make contact with the inner wall of upstanding sleeve 78, to provide frictional securance, and further assurance of retention of the two components together in a locked, flow permitting relationship, so that the contents of syringe 32 b can flow into tubular member 12 b, which may comprise part of a set for the transport of blood or parenteral solutions. If desired, the circular aperture-defining retention zone 28 b of retention wall 72 may be serrated to facilitate a digging-in action for retention of male luer 34 b.

Referring to FIGS. 7–9, an injection or access site in accordance with this invention is shown, which site 66 connects with a conventional luer lock connector 68, or alternatively can connect with a luer slip connector or a sharp or blunt metal cannula, among other things. Injection site 66 is shown connected on the end of flexible tubing 71, which may be connected as part of a tubular parenteral solution or blood set, for example as a Y or T connection with the main flow path of the set. This type of valve may be beneficial for use for the administration of heparin in hemodialysis sets.

Access site 66 comprises a lower housing 73 upon which the periphery of an elastomeric wall 75 is seated, in a manner similar to previous embodiments. A cover 77 is carried on housing 73, and bonded thereto in a conventional manner. In this embodiment, retention wall 79 comprises an upstanding wall portion having a pair of diametrically opposed openings 81, one of which is shown in FIG. 7, so that a pair of conical wall sections 83 comprise retention wall 79, and define the central opening 83 that exposes the central portion of elastomeric wall 75. Elastomeric wall 75 is peripherally retained between housing 73 and cover 77 in a manner similar to previous embodiments, while the central portion of elastomeric wall 75 is exposed.

It can also be seen that the central portion 84 of elastomeric wall 75 defines a dome shape in its normal, unstretched configuration as shown in FIG. 7 (Relative to FIG. 8). The purpose of this dome shape is to suppress backflow of fluid through perforated slit 86 when the interior of housing 73 is pressurized relative to the region above slit 86. This pressure resistance can preferably be on the order of 1500 millimeters of mercury (mm. Hg), so that blood or the like will not normally bleed outwardly from injection site 66 when the set which carries it is filled with blood.

Referring to FIG. 8, the situation is shown where luer lock connector 68, commonly attached to a flexible tube of another medical fluid flow set, has engaged with injection site 66. Male luer portion 88 passes into the central opening of retention wall 79, while connector sheath portion 90 has screw threads which engage the opposed lugs 92 of retention wall 78, in a generally conventional manner. Male luer 88 advances to deform and depress elastomeric wall 75 but, in this embodiment, when male luer 88 is in its fully advanced position as shown in FIG. 8, its fully advanced position is not enough to cause slit 86 of elastomeric wall 75 to open, so that even in this situation a normal outward pressure 94 from blood pumping within injection site 66 and tube 71 is generally insufficient to cause fluid flow through slit 86 to enter into the bore 96 of male luer 88.

However, see FIG. 9, which shows the device of FIG. 8 in a similar configuration except for a change in the pressure situation 98. When pressure 98 is present in bore 96, this pressure, (such as 80–100 mm. of mercury or more) may be capable of opening slit 86 because of the geometry of elastomeric wall 74, permitting the flow of fluid through elastomeric wall 75 in the direction of arrow 98 from luer lock connector 68 into tubing 71, and from there into the fluid flow set to which it is attached. Accordingly, while fluid flow in either direction is not possible at typical pressures in the FIG. 7 situation, unidirectional fluid flow at relatively low pressure is possible in the situation of FIGS. 8 and 9, because of the distortion of elastomeric wall 75 caused by engagement with male luer 88, so that flow at pressures used in direction 94 is not possible, while flow in direction 98 is readily available when desired.

FIGS. 8 and 9 utilize a connector wall 79 having a bore 100 which is of a conical shape of a different and slightly larger angle than the conical shape of male luer 88. Thus, there may be no full, annular contact between the wall of conical bore 100 and male luer 88 in area 102, (FIG. 8) while there is firm contact, generally with distortion of material to provide a generally releasable bond between the surfaces of bore 100 and male luer 88, in area 104. This provides an annular seal, typically less than 3 mm in axial thickness, resulting in a second seal above and beyond annular seal 106 between the tip of male luer 88 and elastomeric wall 75, and also increases the retention due to the deformation of material in the bonding area 104. This is particularly useful if a luer slip connector is used instead of luer lock connector 68, since an increase in locking retention force of the connection is provided.

Alternatively, conical bore surface 100 may receive a standard cylindrical connector tube to provide a similar bond, with material distortion in area 104 with such tube. Alternatively, surface 100 may be cylindrical, and may engage a portion of a tapered connector tube to provide a similar, material-deforming bond, as may be desired.

In summary, the cracking pressure of perforation 86 is decreased by the mating of typically a luer slip or luer lock connector, the latter being shown in FIGS. 8 and 9, but the slit 86 is still closed until a sufficient overpressure upstream 98 is applied. Blood is also prevented from passing back into a syringe attached to luer lock connector 68 by means of the blood pump pulsing of a conventional hemodialysis circuit, which may transitorily cause a downstream pressure 94 which is greater than the upstream pressure.

A purpose of the diametrically opposed openings 81 is to provide access for sterile swabbing of the top of elastomeric wall. These apertures are optional, and may be dispensed with, especially in a clinical situation where it is not intended that a connection with injection site 66 is to be made more than once. Swabbing for resterilization is usually needed only in a situation where injection site 66 is used multiple times, since, typically, it will be initially provided to the user in sterile condition.

Referring to FIG. 10, an injection site and connector 110 is shown, comprising a housing 112, which is closed at the top by elastomeric wall 114 having a perforated slit 116 as in previous embodiments. Elastomeric wall 114 is retained in its position in manner similar to previous embodiments, being held on annular ledge 118 of housing 112 by a cover 120, which acts as the retention wall, as previously discussed, and defines annular retention zone 122, which, in turn, defines central opening 124.

It can be seen that retention zone 122 defines a minimum diameter area at its bottom, next to elastomeric wall 114, with the diameter tapering outwardly as one draws farther away from elastomeric wall 114.

Luer slip connector 126 may comprise the front end of a syringe 128, or it may comprise the part of any other desired device, connected to a medical fluid flow set if desired. Luer slip 126 typically meets ISO standards.

As shown in FIG. 11, luer slip connector 126 is advanced through central opening 124, with the tapered connector 126 engaging annular retention zone 122 completely about the periphery of luer slip connector 126. In this embodiment, the material of retention wall 20 and retention zone 122 may be made of polycarbonate plastic, having a Rockwell hardness of about M 60, and being significantly harder than a typically polypropylene luer slip connector 126. Thus, as indicated in FIG. 11, as connection is made, the luer slip connector tube 126 is deformed by the harder material of the retention zone 122, so that the retention zone deforms or digs into the material of luer slip connector 126, thus increasing the strength of retention between the retention wall 120 and connector tube 126. At the same time, as FIG. 11 shows, a central portion of elastomeric wall 114 is displaced and stretched by the advancing connector tube 126 to stretch open perforated slit 116, so that flow communication becomes possible between housing 112 and its connected, flexible tube 113, and syringe 128.

In this embodiment, the minimum diameter of retention zone 122 is adjusted to allow connector tube 126 to penetrate to a depth where not only does the end 130 of connector tube form a first, annular seal at 130 against the upper surface of elastomeric wall 114, but connector tube 126 can penetrate to such a depth that a second, annular side seal 132 is also formed between elastomeric wall 114 and connector tube 126, before forward motion of tube 126 is terminated by firm engagement and material deformation between tube 126 and retention zone 122.

It can be seen that the diameter of retention zone 122 can thus vary the type of connection and seal that is formed between elastomeric wall 114 and tube 126. In FIGS. 8 and 9, for example, it can be seen that the permitted depth of penetration of connector tube 88 is such that only a single, annular end seal at 106 is provided between the elastomeric wall and the connector tube 88. In the situation of FIG. 11, if the minimum diameter of retention zone 122 is a little smaller, then that same situation will take place as in FIGS. 8 and 9.

In contrast, FIG. 12 shows a connection between injection site/connector 110 a and a conventional luer lock connector 134, which may be of ISO specification, and may be connected to a syringe 136, a tubular flow set connection, or any other desired device. As in the previous embodiment of FIGS. 7–9, tapered luer connector 138 may engage with the bore of similarly or differently tapered female retention wall locking sleeve 140, which conventionally locks with the threads 139 of luer connector 134. The bore 142 of locking sleeve 140 may be tapered at an angle slightly larger than the 6% luer taper of connector tube 138, so that, as in FIGS. 8 and 9, a lower portion 144 of bore 142 engages luer connector tube 138, with deformation of material, while at portion 146 of bore 142 the two surfaces do not deform and may even be slightly spaced. Typically, retention wall sleeve 140, as part of elastomeric wall retention cap 148, is made of harder material than luer connector tube 138, but, if desired, the converse can be true, with the deformation of material providing an annular, sealed retention zone at 144 with added resistance to separation.

In this embodiment, the minimum diameter of bore 142 is such that male luer 138 may penetrate elastomeric wall 114 a (which may be essentially identical to elastomeric wall 114 if desired) to a degree greater than the penetration illustrated in FIG. 11, opening perforated slit 116 a more widely than in the previous embodiment and providing a deeper annular, peripheral seal 132 a around the side of tube 138, along with the abutting annular seal 130 a at the end of tube 138.

Thus, the depth of penetration of the connector tube into the elastomeric wall can be governed by the diameter of the retention zone 122, 144, etc. Furthermore, the injection site/connector of this invention is very tolerant as to dimensional variation in molding, since the system has tolerance for the specific position of advancement of tube 126, 138 into connector 110, 110 a. The situation of FIG. 2 can be created by one diameter of the retention zone; the situation of FIG. 11 created by another such diameter; and the situation of FIG. 12 can be created by a third diameter of the retention zone.

Retention wall 140 may comprise a complete sleeve, or it may carry slots in a manner similar to that shown in FIG. 7 for the purpose of permitting effective, easy swabbing of the outer surface of the elastomeric wall prior to reuse. Also, as discussed, variation in the depth of penetration by the connector tube may be controlled by adjustment of the diameter of the connector tube.

Referring to FIG. 13, injection site/connector 110 b may be of similar design to the previous connector 110 a. In this embodiment, a male luer lock connector 150 is shown, having a conventional, rotatable, threaded male luer locking sleeve 152, which is shown to be threadedly engaging opposed lugs 154, carried on sleeve 156, which defines the retention wall. Sleeve 156, in this embodiment, has no side apertures as in previous embodiments, but comprises an intact sleeve with a tapered bore which may be of slightly larger angle than the tapered outer diameter of the lower tip 158 of connector tube 160.

As in the previous embodiment, at lower bore section 144 a, the material at the junction of tapered tube 158 and tapered bore 142 a is deformed by engagement so that the area 144 a becomes the retention zone, holding the connection together with increased force to supplement the threaded retention of this system.

Additionally, the diameter of retention zone 144 a is adjusted so that tapered tube 158 penetrates to a greater degree than in the previous embodiments, as shown, to widely open perforated slit 116 b of elastomeric wall 114 b, to approximate the diameter of the rest of the flow lumen as found in connected tubing 159 and bore 160 of tapered tubing 158. This embodiment is particularly useful in providing a generally laminar flow path, which is particularly desirable for the flow of blood and the avoidance of clotting. Also, it can be seen that a relatively large retention zone 144 a and relatively large annular side seal 162 may be provided where the front end of tapered tube 158 passes through elastomeric wall 114 b and partially through the slit.

The almost-penetrated elastomeric wall 114 b serves as a transition seal and flow guide between the annular end face 163 of the connector tube 158 and the lumen wall 165 of the adjacent bore of connector 110 b. In typical male/female connector sets, the flow path defines an annular “step” between the connector tube and the adjacent bore of the female connector, creating significant turbulence and pressure loss, dependent on the size of annular end face 163. By this invention, such a “step” is largely avoided, thus reducing turbulence and pressure loss.

Each of the embodiments of FIGS. 10–13 may either carry a retention sleeve such as sleeve 140 in FIGS. 12 and 156 in FIG. 13, or such a sleeve may be eliminated as in the embodiment of FIGS. 10 and 11, while still retaining the significant and improved retention of the connection because of the deformation of material achieved in the connection.

In all embodiments, upon withdrawal of the connector tube, the elastomeric wall can typically reclose its perforated slit to provide resealing again of the interior of the injection site/connector of this invention.

The above has been offered for illustrative purposes only, and is not intended to limit the scope of the invention of this application, which is as defined in the claims below. 

1. A medical device having an interior for containment of fluids; an opening into the interior; an elastomeric wall comprising a fixedly placed, flexible barrier across said opening; and a retention wall positioned adjacent to a peripheral portion of said elastomeric wall, said retention wall defining a central opening, said retention wall having a generally rigid retention zone surrounding said central opening, to engage and retain a connector tube having a leading end which is advanced into said central opening to displace said elastomeric wall to weaken the resistance to flow of a closed perforation extending substantially through said elastomeric wall, said retention zone being sized to engage and hold said connector tube before said leading end completely penetrates said elastomeric wall, whereby the perforation of said elastomeric wall remains sealed, but can be opened for fluid flow by application of a low pressure differential in one direction to cause fluid flow through the perforation of said elastomeric wall, while said elastomeric wall exhibits a substantially higher resistance to said fluid flow under pressure when said elastomeric wall is not displaced by said connector tube.
 2. The medical device of claim 1 in which one of said retention zone and connector tube is made of a material of sufficient hardness that material of the other of said retention zone and said engaged and retained connector tube is deformed by engagement therewith, to increase strength of retention between the retention wall and the connector tube.
 3. The device of claim 2 in which said retention zone is ring shaped, and has an axial depth of no more than about 3 mm.
 4. The device of claim 3 in which a plurality of spaces divides said retention zone into separate sections.
 5. The device of claim 1 in which the material of the retention zone has a hardness of at least about Shore A
 80. 6. The device of claim 1 in which said retention wall is spaced from the elastomeric wall.
 7. The device of claim 1 in which said retention zone has an axial depth of no more than about 1 mm.
 8. A medical device having an interior for containment of fluids; an opening into the interior; an elastomeric wall comprising a fixedly placed, flexible barrier across said opening; and a retention wall positioned adjacent to a peripheral portion of said elastomeric wall, said retention wall defining a central opening, said retention wall having a generally rigid retention zone surrounding said central opening, a connector tube engaged with and retained by said retention zone, said connector tube having a leading end which is advanced into said central opening to displace said elastomeric wall to weaken the resistance to flow of a closed perforation extending substantially through said elastomeric wall, said retention zone being sized to engage and hold said connector tube before said leading end completely penetrates said elastomeric wall, whereby the perforation of said elastomeric wall remains sealed, but can be opened for fluid flow by application of a low pressure differential in one direction to cause fluid flow through the perforation of said elastomeric wall, while said elastomeric wall exhibits a substantially higher resistance to said fluid flow under pressure when said elastomeric wall is not displaced by said connector tube.
 9. The medical device of claim 8 in which one of said retention zone and connector tube is made of a material of sufficient hardness that material of the other of said retention zone and said engaged and retained connector tube is deformed by engagement therewith, to increase strength of retention between the retention wall and the connector tube.
 10. The device of claim 9 in which said retention zone is ring-shaped, and has an axial depth of no more than about 3 mm.
 11. The device of claim 10 in which a plurality of spaces divides the said retention zone into separate sections.
 12. The device of claim 8 in which the material of the retention zone has a hardness of at least about Shore A80.
 13. The device of claim 8 in which said elastomeric wall, when not displaced, can resist flow up to a pressure of about 1,500 mmHg, and when displaced by said connector tube said perforation can open in at least one direction at a pressure of at least about 80 mmHg.
 14. The device of claim 8 in which said retention wall is spaced from the elastomeric wall.
 15. The device of claim 8 in which said retention zone is ring-shaped, and has an axial depth of no more than about 3 mm.
 16. The device of claim 15 in which a plurality of spaces divides said retention zone into separate sections.
 17. The device of claim 15 in which the material of the retention zone has a hardness of at least about Shore A80.
 18. The device of claim 17 in which said elastomeric wall, when not displaced, can resist flow up to a pressure of about 1,500 mmHg, and when displaced by said connector tube, said perforation can open in at least one direction at a pressure of at least about 80 mmHg.
 19. The device of claim 18 in which said retention wall is spaced from the elastomeric wall.
 20. The device of claim 8 in which said retention zone has an axial depth of no more than about 1 mm.
 21. A medical device having an interior for containment of fluids; an opening into the interior; an elastomeric wall comprising a fixedly placed, flexible barrier across said opening; and a retention wall positioned adjacent to a peripheral portion of said elastomeric wall, said retention wall defining a central opening, said retention wall having a generally rigid retention zone surrounding said central opening, to engage and retain a connector tube having a leading end which is advanced into said central opening to displace said elastomeric wall to weaken the resistance to flow of a closed perforation extending substantially through said elastomeric wall, said retention zone being sized to engage and hold said connector tube before said leading end completely penetrates said elastomeric wall, whereby the perforation of said elastomeric wall remains sealed, but can be opened for fluid flow by application of a low pressure differential in one direction to cause fluid flow through the perforation of said elastomeric wall, while said elastomeric wall exhibits a substantially higher resistance to said fluid flow under pressure when said elastomeric wall is not displaced by said connector tube; in which said elastomeric wall, when not displaced, can resist flow up to a pressure of about 1,500 mmHg and, when displaced by said connector tube, said perforation can open in at least one direction at a pressure of at least 80 mmHg.
 22. The device of claim 21 in which said retention zone has an axial depth of no more than about 1 mm. 